Apparatus for non-invasive blood glucose monitoring

ABSTRACT

An apparatus for non-invasive blood glucose monitoring includes a light source for generating at least one ray of light, a beam splitter with a focusing function leads the light into an eyeball and focuses on the eyeball, a set of photo detectors for measuring optical angular information and absorption energy information of the light reflected from the eyeball and transmitted through the first beam splitter to the set of photo detectors, and a processing unit. The processing unit receives and processes the Optical angular information and the absorption energy information to obtain an Optical angular difference and an absorption energy difference between the light emitted from the light source and the light transmitted to the set of photo detectors, and analyzes the Optical angular difference and the absorption energy difference to obtain a glucose information, and since the glucose information has a corresponding relationship with a blood glucose information, the blood glucose information may be read.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims the priority benefits of U.S. provisionalapplication Ser. No. 61/480,386, filed on Apr. 29, 2011 and U.S.provisional application Ser. No. 61/508,078, filed on Jul. 15, 2011.This application is also related to the copending patent applicationsidentified in the following chart.

U.S. patent application Ser. No. Filing Date 13/457,517 Apr. 27, 201214/141,459 Dec. 27, 2013 14/141,472 Dec. 27, 2013

The entirety of each of the above-mentioned patent applications ishereby incorporated by reference herein and made a part of thisspecification.

TECHNICAL FIELD

The disclosure relates to an apparatus for glucose monitoring, in moreparticular, to an apparatus for non-invasive glucose monitoring.

BACKGROUND

Diabetes is a clinical syndrome caused by factors such as absolute orrelative lack of insulin in the body, abnormal secretion time, ordisorder or resistance of insulin effector, etc. If the diabetes is notsuitably controlled, it may cause some acute complications such ashypoglycemia, ketoacidosis, nonketotic hyperosmolar coma, etc. Theserious long-term complications include cardiovascular diseases, chronicrenal failure, retinopathy, neuropathy and microvascular diseases, etc.

Constant blood glucose monitoring is very important for diabetics. Aprimary objective of treating the diabetic is to maintain a normalconcentration of glucose, and if a patient carefully controls bloodglucose daily, occurrence of the above complications may be effectivelyprevented.

Presently, the diabetic generally use blood glucose monitor to monitorthe blood glucose. However, before the blood glucose monitor is used tomeasure a concentration of blood glucose, blood collection has to befirst performed. Fingertip pricks are an invasive (destructive) samplingmethod for blood collection, and a process thereof is complicated andmay cause pain, which is also an important reason why the diabeticcannot periodically monitor the blood glucose.

Therefore, a method for non-invasive blood glucose monitoring becomes adevelopment trend in blood glucose detection. The existing non-invasiveglucose meters measure the blood glucose through a single method (forexample, an acoustic method, an optical method or an electrical method),though the measurements are mainly performed in allusion to skin bloodglucose of human body. However, the skin is composed of epidermis,dermis, subcutaneous tissues, and different tissues, blood vessels andwater in the skin may produce scattering light and absorption light,which may influence signal measurement, and accordingly influence theaccuracy of measured blood concentration of glucose.

SUMMARY

The disclosure provides an apparatus for non-invasive glucose monitoringcomprising a light source, a first beam splitter, a set of photodetectors, and a processing unit. The light source generates at leastone ray of light. The first beam splitter with a focusing function leadsthe light emitted from the light source into an eyeball and focuses onthe eyeball through the first beam splitter. The set of photo detectorsmeasures an optical angular information and an absorption energyinformation of the light, which are reflected from the eyeball and thentransmitted through the first beam splitter to the set of photodetectors. The optical angular information may be the optical angularinformation of a polarized light passing through a polarizer. Theprocessing unit receives and processes the optical angular informationand the absorption energy information to obtain an optical angulardifference and an absorption energy difference between the light emittedfrom the light source and the light transmitted to the set of photodetectors, and to obtain biological molecule information, which at leastcomprises a glucose, by analyzing the optical angular difference and theabsorption energy difference. The processing unit obtains a glucoseinformation through analyzing the biological molecule information, andsince the glucose information has a corresponding relationship with ablood glucose information, the blood glucose information may be read.

The disclosure provides a portable mobile device with a non-invasiveblood glucose monitoring function, comprising a device body, at leastone light source, an optical kit, a set of photo detectors, and aprocessing unit. The light source generates at least one ray of light.The optical kit disposed on the device body comprises a first beamsplitter therein, and the first beam splitter with a focusing functionwhich can lead the light emitted from the light source into an eyeballand focus on the eyeball through the first beam splitter. The set ofphoto detectors measures an optical angular information and anabsorption energy information of the light, which are reflected from theeyeball and then transmitted through the beam splitter to the set ofphoto detectors. The processing unit disposed in the device bodyreceives and processes the optical angular information and of theabsorption energy information obtain an optical rotatory angulardifference and an absorption energy difference between the light emittedfrom the light source and the light transmitted to the set of photodetectors, and to obtain biological molecule information, which at leastcomprises a glucose, by analyzing the optical angular difference and theabsorption energy difference. The processing unit obtains glucoseinformation by analyzing the biological molecule information. As theglucose information is related to blood glucose information, the bloodglucose information may be read.

Several exemplary embodiments accompanied with figures are described indetail below to further describe the disclosure in details.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings are included to provide further understanding,and are incorporated in and constitute a part of this specification. Thedrawings illustrate exemplary embodiments and, together with thedescription, serve to explain the principles of the disclosure.

FIG. 1A is a schematic diagram illustrating an apparatus fornon-invasive glucose monitoring in accordance with a first exemplaryembodiment.

FIG. 1B is a schematic diagram illustrating an optical rotatorydistribution measuring device in FIG. 1A.

FIG. 2 is a schematic diagram illustrating an apparatus for non-invasiveglucose monitoring in accordance with a second exemplary embodiment.

FIG. 3 is a schematic diagram illustrating an apparatus for non-invasiveglucose monitoring in accordance with a third exemplary embodiment.

FIG. 4 is a schematic diagram illustrating an apparatus for non-invasiveglucose monitoring in accordance with a fourth exemplary embodiment.

FIG. 5 is a flow chat diagram illustrating a method for a non-invasiveblood glucose monitoring in accordance with a fifth exemplaryembodiment.

FIG. 6 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with asixth exemplary embodiment.

FIG. 7 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with aseventh exemplary embodiment.

FIG. 8 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with aneighth exemplary embodiment.

FIG. 9 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with aninth exemplary embodiment.

FIG. 10 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance witha tenth exemplary embodiment.

FIG. 11 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance witha eleventh exemplary embodiment.

FIG. 12 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance witha twelfth exemplary embodiment.

FIG. 13 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance witha thirteenth exemplary embodiment.

FIG. 14 is a schematic diagram illustrating a method for analyzingbiological molecule in accordance with a fourteenth exemplaryembodiment.

DETAILED DESCRIPTION OF DISCLOSED EMBODIMENTS

The disclosure provides an apparatus for non-invasive glucose monitoringcapable of accurately measure a glucose information (e.g., concentrationof glucose) of a measuring object, and since the glucose information(e.g., concentration of glucose) in an eyeball (e.g., aqueous humorwithin eyeball) has a corresponding relationship with a blood glucoseinformation (e.g., concentration of blood glucose), the blood glucoseinformation (e.g., concentration of blood glucose) may be read.

The disclosure also provides a method for non-invasive blood glucosemonitoring to measure concentration of glucose in real time.

FIG. 1A is a schematic diagram illustrating an apparatus fornon-invasive glucose monitoring in accordance with a first exemplaryembodiment. FIG. 1B is a schematic diagram illustrating an opticalrotatory distribution measuring device from FIG. 1A in accordance withthe first exemplary embodiment.

With reference to FIG. 1A, an apparatus for non-invasive glucosemonitoring 100 which comprises a light source 102, an optical kitincluding a first beam splitter 104, a set of photo detectors 106, and aprocessing unit 108. The apparatus for non-invasive blood glucosemonitoring 100 may, for example, detect concentration of glucose of anaqueous humor 204 in an anterior chamber 202 of an eyeball 200.

The light source 102 generates at least one ray of light 110. The lightsource 102 is, for example, a light emitting diode (LED), a laser diode,or other light source. A wavelength of the light source 102 is, forexample, which can be absorbed by glucose molecules, and namely, awavelength that is capable of being absorbed by the glucose molecules inthe eyeball 200, such as an infrared light. The light 110 emitted fromthe light source 102 comprises a linear polarized light, a circularpolarized light, an elliptical polarized light, or a partial polarizedlight. Moreover, the light source 102 may have a function forcontrolling an emitting frequency of the light 110, which avails thephoto detector set 106 in determining the light to be measured accordingto the emitting frequency. In addition, the light source 102 may have afunction for controlling an intensity of the light 110, which assuresthe light entering into the eyeball 200 is unable to cause any harm.Furthermore, the light source 102 may have a function for controlling alength of turn-on time of the light 110 and controlling a length ofturn-off time of the light 110, or a combination thereof, which providesa glucose detection time on one hand but also ensures that the lightenergy entering into the eyeball 200 is unable to cause any harm on theother hand. Although, in the present exemplary embodiment, the singlelight 110 emitted from the single light source 102 is taken as anexample for description, the disclosure is not limited thereto; and, inanother exemplary embodiment, types of the light source 102 and types ofthe light 110 may be two or more.

The first beam splitter 104 with a focusing function which can lead thelight 110 emitted from the light source 102 into an eyeball 200 andfocus on the eyeball 200 through the first beam splitter 104. The firstbeam splitter 104 is, for example, focusing the light 110 onto theanterior chamber 202 of the eyeball 200, and the light 110 reflectedfrom the eyeball 200 comprises the light reflected from the aqueoushumor 204. The first beam splitter 104 is, for example, an optical film,a lens, a grating, a diffractive optic device or a combination of anythe above elements.

The set of photo detectors 106 measures an optical rotatory distributioninformation and an absorption energy information of the reflected light111 reflected from the eyeball 200 and then transmitted through thefirst beam splitter 104 to the set of photo detectors 106. In thepresent exemplary embodiment, the set of photo detectors 106 comprisesan optical rotatory distribution measuring device 112 and an energymeasuring device 114. Wherein, the optical rotatory distributionmeasuring device 112 is used for measuring the optical rotatorydistribution information of the reflected light 111 reflected from theeyeball 200 and then transmitted through the first beam splitter 104,and the energy measuring device 114 is used for measuring the absorptionenergy information of the reflected light 111 reflected from the eyeball200 and then passed through the first beam splitter 104.

In another exemplary embodiment, the optical rotatory distributionmeasuring device 112 and the energy measuring device 114 may beexchanged. Namely, the optical rotatory distribution measuring device112 is used to measure the optical rotatory distribution information ofthe reflected light 111 reflected from the eyeball 200 and then passedthrough the first beam splitter 104, and the energy measuring device 114is used to measure the absorption energy information of the reflectedlight 111 reflected from the eyeball 200 and then reflected by the firstbeam splitter 104.

With reference to FIG. 1B, the optical rotatory distribution measuringdevice 112 comprises a polarizer 112 a and a light sensing element 112b, wherein the light is firstly passed through the polarizer 112 a, andthen transmitted to the light sensing element 112 b. The opticalrotatory distribution measuring device 112 is, for example, an activeoptical rotatory distribution measuring device or a passive opticalrotatory distribution measuring device, wherein a measurement angle ofthe active optical rotatory distribution measuring device may be changedwhereas a measurement angle of the passive optical rotatory distributionmeasuring device is fixed. The active optical rotatory distributionmeasuring device is, for example, an analyzer which may directlycalculate the optical rotatory distribution information. The passiveoptical rotatory distribution measuring device measures the energy ofthe reflected light 111 that passed through a polarizer 112 a using thelight sensing element 112 b to calculate the angular information of theoptical rotatory distribution information. The energy measuring device114 is, for example, a light sensing element such as a charge coupleddevice (CCD), a complementary metal oxide semiconductor sensors or alight emitting diode.

Moreover, with reference to FIGS. 1A and 1B, the apparatus fornon-invasive glucose monitoring 100 may further selectively comprise atleast one of a light barrier 113 and a light barrier 115. The lightbarrier 113 has an opening 113 a, and the opening 113 a, throughassembly, may enable the reflected light 111 to pass through the lightbarrier 113, and then transmit to the light sensing element 112 b. Thelight barrier 113 is, for example, disposed between the polarizer 112 aand the light sensing element 112 b, but the disclosure is not limitedthereto. In other exemplary embodiments, the light barrier 113 mayfurther enable the reflected light 111 to pass through the polarizer 112a and then through the opening 113 a of the light barrier 113. Inaddition, the light barrier 115 has an opening 115 a, and the opening115 a, through assembly, may enable the reflected light 111 to passthrough the light barrier 115, and then transmit to the energy measuringdevice (e.g., light sensing element). The light barriers 113, 115respectively are, for example, a metal photomask or a silica glassphotomask. The light barriers 113, 115 respectively may prevent straylight from entering into the optical rotatory distribution measuringdevice 112 and the energy measuring device 114, and thus may reduceinterference from the stray light, so as to enhance the signal to noiseratio (S/N ratio). It is noted that each of the following exemplaryembodiments, through the light barrier, may reduce the influence ofstray light on the measurement results of the optical rotatorydistribution measuring device and of the energy measuring device;however, further elaboration on the light barrier in the other exemplaryembodiments are omitted in order to simplify the description.

Referring to FIG. 1A again, the processing unit 108 is, for example,coupled to the optical angular measuring device 112 and the energymeasuring device 114 of the set of photo detectors 106, and receives andprocesses the optical angular information and the absorption energyinformation to obtain an optical angular difference and an absorptionenergy difference between the light 110 emitted from the light source102 and the light 110 transmitted to the set of photo detectors 106, andto obtain biological molecule information, which at least comprises aglucose, by analyzing the optical angular difference and the absorptionenergy difference. The processing unit obtains the glucose informationthrough analyzing the biological molecule information. The biologicalmolecule is, for example, cholesterol, uric acid, water, lactic acid,urea, ascorbic acid, or a combination thereof. Moreover, the biologicalmolecule may comprise one kind of interference molecules therein, andthe kind of interference molecule is, for example, one kind of moleculedifferent from the measurement target (e.g., glucose), such ascholesterol, uric acid, water, lactic acid, urea, or ascorbic acid. Asascorbic acid and lactic acid may generate interference onto the opticalangular information, whereas water may generate interference to theabsorption energy information. During the process of obtaining theglucose information through the processing unit 108, the processing unit108 may remove interference caused by the interference molecules. Theprocessing unit 108 may also control a light source variation, anopto-element offset or a combination thereof, and statistically analyzethe optical angular information and the absorption energy information,so as to obtain the glucose information. The spatial variation of thelight source comprises a light emitting frequency variation, a lightenergy intensity variation, a length variation of turn-on time of thelight, a length variation of turn-off time of the light, or acombination thereof. Since the glucose concentration in the eyeball 200(e.g., aqueous humor within eyeball) has a corresponding relationshipwith a blood glucose concentration, the blood glucose information (e.g.,blood glucose value) can be determined according to the relationship.The processing unit 108 is, for example, an analog digital circuitintegration module, wherein the analog digital circuit integrationmodule comprises a microprocessor, an amplifier and an analog digitalconverter (ADC). The analog digital circuit integration module mayfurther comprise a wireless transmission device.

In the present exemplary embodiment, the processing unit 108 is, forexample, coupled to the light source 102 to control an opticalcharacteristic of the light 110 emitted from the light source 102.

The apparatus for non-invasive blood glucose monitoring 100 mayselectively comprise a light information analysis unit 116 for detectinga light information of the light 110 from the first beam splitter 104before the light 110 is transmitted into the eyeball 200, andselectively transmit the light information of the light 110 to theprocessing unit 108 or an alarm 118 to perform a feedback control withthe optical characteristic of the light 110. The light informationanalysis unit 116 comprises at least one of an optical power meter andan optical sensor, the light information detected by the optical powermeter is energy information whereas the light information detected bythe optical sensor is at least one of energy information or positioninformation. The optical characteristic of the light 110 is, forexample, energy emittance and/or light position.

When the emitting energy of the light 110 emitted from the light source102 is excessively high, the light 110 may cause harm to the eyeball200. Therefore, when die processing unit 108 receives the energyinformation indicating excessive emitting energy of the light 110, theprocessing unit 108 will reduce the emitting energy of the light 110emitted from the light source 102. On the other hand, when the alarm 118receives the energy information indicating excessive emitting energy ofthe light 110, the alarm 118 sends a light or a sound warning signal tonotify the user that the emitting energy of the light 110 emitted fromthe light source 102 is excessively high, and the emitting energy of thelight 110 should be adjusted. Therefore, usage of the light informationanalysis unit 116 may prevent harming the eyeball 200 due to excessiveemitting energy of the light 110.

Moreover, when the light position of the light 110 emitted from lightsource 102 is shifted, the accuracy of a blood glucose measurement islowered. Therefore, when the processing unit 108 receives the positioninformation indicating the light position of the light 110 is shifted,the processing unit 108 adjusts the light position of the light 110emitted from the light source 102. On the other hand, when the alarm 118receives the position information indicating the light position of thelight 110 is shifted, the alarm 118 sends the light or the sound warningsignal to notify the user that the light position of the light 110emitted from the light source 102 is shifted, and the light position ofthe light 110 should be adjusted. Therefore, usage of the lightinformation analysis unit 116 may prevent the light position of thelight 110 from shifting, thus enhancing the accuracy of the bloodglucose measurement.

In the present exemplary embodiment, the energy information detected bythe light information analysis unit 116 is simultaneously transmitted tothe processing unit 108 and the alarm 118; nevertheless, the feedbackcontrol may be implemented as long as the energy information istransmitted to one of the processing unit 108 and the alarm 118. Thelight information analysis unit 116 is, for example, respectivelycoupled to the processing unit 108 and the alarm 118, but a couplingmanner of the light information analysis unit 116, the processing unit108 and the alarm 118 is not limited thereto.

In another exemplary embodiment, the light source 102 is, for example,coupled to a light source control unit (not shown), and now the lightinformation analysis unit 116 transmits the energy information of thelight 110 to the light source control unit, so as to perform thefeedback control for the light source 102.

In addition, before the light 110 is transmitted into the eyeball 200,the detection of the light 110 reflected by the first beam splitter 104using the light information analysis unit 116 is taken as an example todescribe the present exemplary embodiment.

Furthermore, the apparatus for non-invasive glucose monitoring 100 mayfurther selectively comprise an eye-alignment position device 120 foraligning the sight-line of an eye 122 with the eye-alignment positiondevice 120, so as to determine a measuring position of the eyeball 200.The eye-alignment position device 120 is, for example, a light spot, amarker, or a relief pattern.

On the other band, the apparatus for non-invasive glucose monitoring 100may further selectively comprise a joint element 124. A light outlet ofthe joint element 124, located at the apparatus for non-invasive glucosemonitoring, is used for resting on an outer corer an eye. Moreover, theapparatus for non-invasive glucose monitoring 100 may furtherselectively comprise a protective cover 126 disposed on a surface of thejoint element 124 that is used for resting on the outer corner of eye.The protective cover 126 is, for example, a disposable protective cover.

According to the first exemplary embodiment, the apparatus fornon-invasive blood glucose monitoring 100 may simultaneously analyze theoptical angular difference and the absorption energy difference betweenthe light 110 emitted from the light source 102 and the light 110transmitted to the set of photo detectors 106, thus obtaining theglucose information (e.g., glucose value), and since the glucoseconcentration in the eyeball 200 (e.g., aqueous humor within eyeball)has a corresponding relationship with a blood glucose concentration, theblood glucose information (e.g., blood glucose value) with high accuracyis read through the corresponding relationship.

Moreover, the apparatus for non-invasive blood glucose monitoring 100may be miniaturized in applications, for example, used in form of aheadband or used in collaboration with glasses, so as to improveutilization convenience. In addition, the utilization environment of theapparatus for non-invasive blood glucose monitoring 100 has no specialrestriction, and thus may be utilized indoors or outdoors.

FIG. 2 is a schematic diagram illustrating an apparatus for non-invasiveglucose monitoring in accordance with a second exemplary embodiment.

Referring to FIG. 1A and FIG. 2, a difference between the apparatus fornon-invasive blood glucose monitoring 300 of the second exemplaryembodiment and the apparatus for non-invasive blood glucose monitoring100 of the first exemplary embodiment is that an optical rotatorydistribution measuring device 312 and an energy measuring device 314 ina set of photo detectors 306 of the second exemplary embodiment arelocated at a same side of the first beam splitter 104, and the opticalrotatory distribution measuring device 112 and the energy measuringdevice 114 in the set of photo detectors 106 of the first exemplaryembodiment are located at two sides of the first beam splitter 104,respectively. The optical rotatory distribution measuring device 312 andthe energy measuring device 314 are, for example, coupled to theprocessing unit 108, respectively, but the disclosure is not limitedthereto. Compositions, coupling relations and functions of the othercomponents of the apparatus for non-invasive blood glucose monitoring300 of the second exemplary embodiment are similar to that of theapparatus for non-invasive blood glucose monitoring 100 of the firstexemplary embodiment, so that detailed descriptions thereof are notrepeated.

In the present exemplary embodiment, the set of photo detectors 306 is,for example, used to measure the light 110 reflected from the eyeball200 and then reflected by the first beam splitter 104. The light 110 tobe measured is first transmitted to the optical angular measuring device312 for measuring the optical angular information, and then transmittedto the energy measuring device 314 for measuring the absorption energyinformation. In another exemplary embodiment, the set of photo detectors306 may also be used to measure the light 110 reflected from the eyeball200 and then passed through the first beam splitter 104.

In another exemplary embodiment, the apparatus for non-invasive bloodglucose monitoring 300 further comprises another set of the opticalangular measuring device 312 and the energy measuring device 314, sothat the apparatus for non-invasive blood glucose monitoring 300 has twosets of the optical angular measuring device 312 and the energymeasuring device 314 for respectively measuring the optical angularinformation and the absorption energy information of the light 110reflected from the eyeball 200 and then passed through the first beamsplitter 104, and for measuring the optical angular information and theabsorption energy information of the light 110 reflected from theeyeball 200 and then reflected by the first beam splitter 104.

Similarly, the apparatus for non-invasive blood glucose monitoring 300of the second exemplary embodiment may simultaneously analyze theoptical angular difference and the absorption energy difference betweenthe light 110 emitted from the light source 102 and the light 110transmitted to the set of photo detectors 306 to obtain the glucoseinformation (e.g., glucose value), and since the concentration ofglucose in the eyeball 200 (e.g., aqueous humor within eyeball) has arelationship with a blood glucose concentration, the blood glucoseinformation (e.g., blood glucose value) with a high accuracy is readthrough the corresponding relationship. Moreover, the apparatus fornon-invasive blood glucose monitoring 300 may be miniaturized, so thatit is convenient in utilization, and may be utilized indoors oroutdoors.

FIG. 3 is a schematic diagram illustrating an apparatus for non-invasiveglucose monitoring in accordance with a third exemplary embodiment.

Referring to FIG. 1A and FIG. 3, a difference between an apparatus fornon-invasive blood glucose monitoring 400 of the third exemplaryembodiment and the apparatus for non-invasive blood glucose monitoring100 of the first exemplary embodiment is that the apparatus fornon-invasive blood glucose monitoring 400 of the third exemplaryembodiment further comprises a second beam splitter 404, and a set ofphoto detectors 406 comprises a first photo detector 408 and a secondphoto detector 410. Compositions, coupling relations and functions ofthe other components of the apparatus for non-invasive blood glucosemonitoring 400 of the third exemplary embodiment are similar to that ofthe apparatus for non-invasive blood glucose monitoring 100 of the firstexemplary embodiment, so that detailed descriptions thereof are notrepeated.

The second beam splitter 404 transmits the reflected light 111 reflectedfrom the eyeball 200 and then transmitted through the first beamsplitter 104 to the set of photo detectors 406. The second beam splitter404 is, for example, an optical film, an optical lens, an opticalgrating, a diffractive optical element or a combination of any the aboveelements.

The first photo detector 408 is used to measure the light 110 reflectedby the second beam splitter 404, and the second photo detector 410 isused to measure the light 110 passed through the second beam splitter404. The first photo detector 408 comprises an optical angular measuringdevice 412 and an energy measuring device 414, and the second photodetector 410 comprises an optical angular measuring device 416 and anenergy measuring device 418. The light 110 to be measured is, forexample, first transmitted to the optical angular measuring device 412(or 416) for measuring the optical angular information, and thentransmitted to the energy measuring device 414 (418) for measuring theabsorption energy. Composition of the optical angular measuring device412 (or 416) is similar to that of the optical angular measuring device112, and composition of the energy measuring device 414 (or 418) issimilar to the energy measuring device 114, so that descriptions thereofare not repeated. When the first photo detector 408 and the second photodetector 410 in the apparatus for non-invasive blood glucose monitoring400 may simultaneously measure the optical angular information and theabsorption energy, by cross-comparing the obtained two sets of theoptical angular information and the absorption energy, the opticalangular difference and the absorption energy difference between thelight 110 emitted from the light source 102 and the light 110transmitted to the set of photo detectors 406 may be analyzed to obtainthe glucose information (e.g., glucose value), and since the glucoseconcentration in the eyeball 200 (e.g., aqueous humor within eyeball)has a relationship with the concentration of blood glucose, the bloodglucose information (e.g., blood glucose value) with high accuracy isread through the corresponding relationship. The optical angularmeasuring devices 412, 416 and the energy measuring devices 414, 418are, for example, respectively coupled to the processing unit 108, butthe disclosure is not limited thereto.

It is noted that when the optical angular measuring devices 412, 416 areall passive optical angular measuring devices and respectively comprisea polarizer, the polarizers in the optical angular measuring devices412, 416 are, for example, one of a horizontal polarizer and a verticalpolarizer, or two sets of polarizers with known optical angular angles.If the two sets of the polarizers with known optical angular angles areused, one of the measuring methods thereof is to compare energydifferences of the two sets of the polarizers, and according to theenergy differences, the optical angular difference within a certainrange of glucose concentration is obtained, so as to improve thedetection accuracy. Another method is to use the two sets of polarizerswith known optical angular to determine offset components according tothe absorption energy differences, so as to calculate the opticalangular information.

In another exemplary embodiment, one of the first photo detector 408 andthe second photo detector 410 is, for example, a single optical rotatorydistribution measuring device, and another one of the first photodetector 408 and the second photo detector 410 is, for example, a singleenergy measuring device.

Although, in the aforementioned exemplary embodiment, the reflectedlight reflected light 111 by the second beam splitter 404 and/or thereflected light 111 passed through the second beam splitter 404 is oneray of light. However, the reflected light 111 reflected by the secondbeam splitter 404 and/or the reflected light 111 passed through thesecond beam splitter 404 may be divided into two or more rays of lightby the second beam splitter 404, and then measured by the aforementionedfirst photo detector 408 and the second photo detector 410.

According to the third exemplary embodiment, the apparatus fornon-invasive blood glucose monitoring 400 may simultaneously analyze theoptical angular difference and the absorption energy difference betweenthe light 110 emitted from the light source 102 and the light 110transmitted to the set of photo detectors 406 to obtain the glucoseinformation (e.g., glucose value), and since the concentration ofglucose in the eyeball 200 (e.g., aqueous humor within eyeball) has arelationship with the concentration of blood glucose, the blood glucoseinformation (e.g., blood glucose value) with a high accuracy is readthrough the corresponding relationship. Moreover, the apparatus fornon-invasive blood glucose monitoring 400 may be miniaturized, so thatit is convenient in utilization, and thus may be utilized indoors oroutdoors.

FIG. 4 is a schematic diagram illustrating an apparatus for non-invasiveglucose monitoring in accordance with a fourth exemplary embodiment.

Referring to FIG. 3 and FIG. 4, a difference between an apparatus fornon-invasive blood glucose monitoring 500 of the fourth exemplaryembodiment and the apparatus for non-invasive blood glucose monitoring400 of the third exemplary embodiment is that, in the apparatus fornon-invasive blood glucose monitoring 500 of the fourth exemplaryembodiment, a set of photo detectors 506 comprises a first photodetector 508 and a second photo detector 510, and the first photodetector 508 and the second photo detector 510 are located at a sameside of the second beam splitter 404. In the present exemplaryembodiment, the first photo detector 508 and the second photo detector510 are, for example, located at the side of the second beam splitter404 where the light 110 passes there through, and are respectively usedto measure two rays of light 110 a, 110 b generated by the light 110after passed through the second beam splitter 404. One of the firstphoto detector 508 and the second photo detector 510 is, for example, anoptical angular measuring device for measuring the optical angularinformation, and another one of the first photo detector 508 and thesecond photo detector 510 is, for example, an energy measuring devicefor measuring the absorption energy information. The first photodetector 508 and the second photo detector 510 are, for example, coupledto the processing unit 108, respectively, but the disclosure is notlimited thereto. Compositions, coupling relations and functions of theother components of the apparatus for non-invasive blood glucosemonitoring 500 of the fourth exemplary embodiment are similar to that ofthe apparatus for non-invasive blood glucose monitoring 400 of the thirdexemplary embodiment, so that detailed descriptions thereof are notrepeated.

In another exemplary embodiment, the first photo detector 508 and thesecond photo detector 510 may also be located at the side of the secondbeam splitter 404, respectively, where the reflected light 111 isreflected, and are used to measure two rays of light generated byreflecting the reflected light 111 through the second beam splitter 404.

Although, in the aforementioned exemplary embodiment, the light 110reflected by the second beam splitter 404 and/or the light 110 passedthrough the second beam splitter 404 are the reflected light 111 a, 111b, the reflected light 111 reflected by the second beam splitter 404and/or the reflected light 111 passed through the second beam splitter404 may be divided into three or more rays of light by the second beamsplitter 404 and then measured by the aforementioned first photodetector 508 and the second photo detector 510.

Similarly, the apparatus for non-invasive blood glucose monitoring 500of the fourth exemplary embodiment may simultaneously analyze theoptical angular difference and the absorption energy difference betweenthe light 110 emitted from the light source 102 and the light 110 a,100b transmitted to the photo detector set 506 to obtain the glucoseinformation (e.g., glucose value), and since the concentration ofglucose in the eyeball 200 (e.g., aqueous humor within eyeball) has arelationship with the concentration of blood glucose, the blood glucoseinformation (e.g., blood glucose value) with a high accuracy is readthrough the corresponding relationship. Moreover, the apparatus fornon-invasive blood glucose monitoring 500 may be miniaturized, so thatit is convenient in utilization, and thus may be utilized indoors oroutdoors.

FIG. 5 is a flow chat diagram illustrating a method for a non-invasiveblood glucose monitoring in accordance with a fifth exemplaryembodiment.

With reference to FIG. 5, firstly, step S90 may be selected performedfor aiming the eyeball onto the eye-alignment position device to alignthe sight of the eye with the eye-alignment position device forperforming alignment, wherein the alignment includes adjusting arelative angle and a position between the optical axis of theeye-alignment position device and the sight of the eye, so as todetermine a measuring position of the eyeball. Next, in step S100, atleast one ray of light is emitted through at least one light source.Then, step S102 may be selectively performed for controlling the opticalcharacteristic of the light source, the opto-element offset or thecombination thereof, and a change factor is produced thus facilitates inanalyzing the blood glucose information more accurately. Wherein, thelight source is used to control an emitting frequency of the light, anintensity of the light, a length of turn-on time of the light, a lengthof turn-off time of the light, or a combination thereof. The set ofphoto detectors may assure the light to be measured according to theemitting frequency of the light. Moreover, by controlling the intensityof the light through the light source, it is ensured that the lightenergy entering the eyeball is unable to cause any harm. In addition, bycontrolling the length of turn-on time of the light, the length ofturn-off time of the light or the combination thereof through the lightsource, a time required for glucose detection is provided on one hand,and it is ensured that the light energy entering the eyeball is unableto cause any harm on the other hand. Then, step S104 may be selectivelyperformed, by which before the light is directed into the eyeball, thelight information of the light from the first beam splitter is detected,so as to perform a feedback control with the optical characteristic ofthe light. The light information comprises at least one of the energyinformation and the position information. The optical characteristic is,for example, a position for emitting energy and/or light. Next, in stepS106, the light emitted from the light source is directed into theeyeball and focused on the eyeball through the first beam splitter withthe focusing function. Then, one of step S108 and step S110 may beperformed. Wherein, in step S108, the light reflected from the eyeballis transmitted to the set of photo detectors through the first beamsplitter. In step S110, the light reflected from the eyeball istransmitted to the second beam splitter through the first beam splitter,and then the light is transmitted to the set of photo detectors throughthe second beam splitter. Furthermore, in step S112, the optical angularinformation and the absorption energy information of the lighttransmitted to the set of photo detectors are measured by the set ofphoto detectors. Then, in step S114, the optical angular difference andthe absorption energy difference between the light emitted from thelight source and the light transmitted to the set of photo detectors areobtained by processing the optical angular information and theabsorption energy information. Next, in step S116, the optical angulardifference and the absorption energy difference are analyzed to obtainthe information of the biological molecule, wherein the biologicalmolecule at least comprises the glucose, the glucose information isobtained through the biological molecule information, the glucoseconcentration in the eyeball (e.g., aqueous humor within eyeball) has acorresponding relationship with the concentration of blood glucose, theblood glucose information (e.g., blood glucose value) is read throughthe corresponding relationship. The biological molecule is, for example,cholesterol, uric acid, water, lactic acid, urea, ascorbic acid, or acombination thereof. Moreover, the biological molecule may comprise aninterference molecule therein, and the interference molecule is, forexample, different from the measurement target (e.g., glucose), such ascholesterol, uric acid, water, lactic acid, urea, or ascorbic acid.Wherein, ascorbic acid and lactic acid may generate interference to theoptical angular information whereas water may generate interference tothe absorption energy information. Furthermore, in step S116,interference generated by the interference molecule may further beselectively removed. Variations of the method for non-invasive bloodglucose monitoring and various used devices of the fifth exemplaryembodiment have been described in detail in the first to the fourthexemplary embodiments, so that descriptions thereof are not repeated.

According to the above descriptions, in the method for non-invasiveblood glucose monitoring of the fifth exemplary embodiment, since anoptical eyeball detecting method is used to measure the glucoseinformation (e.g., concentration of glucose) of the measuring object,the glucose information (e.g., glucose concentration) of the measuringobject may be continuously obtained in real time, and since the glucoseconcentration has a relationship with a blood glucose concentration, theblood glucose information (e.g., concentration of blood glucose) may beread.

On the other hand, the above-mentioned exemplary embodiment of theapparatus for non-invasive glucose monitoring may further be used in theapplication of a portable mobile device, so that the portable mobiledevice has a non-invasive blood glucose monitoring function. Theportable mobile device is, for example, mobile phone, tablet PC, digitalcamera, and so forth. The following descriptions below are, theexemplary embodiments, for describing a portable mobile device with anon-invasive blood glucose monitoring function.

FIG. 6 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with asixth exemplary embodiment.

Referring to FIG. 2 and FIG. 6, a difference between a portable mobiledevice 600 of the sixth exemplary embodiment and the apparatus fornon-invasive glucose monitoring 300 of the second exemplary embodimentis that the portable mobile device 600 further comprises a device body602 and an optical kit 604. The optical kit 604 is disposed on thedevice body 602, and the optical kit 604 comprises the first beamsplitter 104 therein. A set of photo detectors 606, the processing unit108, the light source 102, the light information analysis unit S116, andthe alarm 118 are, for example, disposed in the device body 602, but thedisclosure is not limited thereto. Moreover, the set of photo detectors606 comprises an optical rotatory distribution measuring device 612 andan energy measuring device 614, wherein the portable mobile device 600uses a light sensing element in a camera module thereof as the energymeasuring device 614 in the set of photo detectors 606. The opticalrotatory distribution measuring device 612 and the energy measuringdevice 614 are, for example, respectively coupled to the processing unit108, but the disclosure is not limited thereto. The optical rotatorydistribution measuring device 612 is, for example, an active opticalrotatory distribution measuring device or a passive optical rotatorydistribution measuring device. The energy measuring device 614 is, forexample, a light sensing element, such as a charge coupled device, acomplementary metal oxide semiconductor sensors or a light emittingdiode. In addition, the light 110 used by the portable mobile device 600for blood glucose monitoring is transmitted through a light route of thecamera module of the portable mobile device 600. Compositions, couplingrelations and functions of the other components of the portable mobiledevice 600 of the sixth exemplary embodiment are similar to that of theapparatus for non-invasive blood glucose monitoring 300 of the secondexemplary embodiment, and the similar components of the portable mobiledevice 600 of the sixth exemplary embodiment and of the apparatus fornon-invasive blood glucose monitoring 300 of the second exemplaryembodiment are with similar compositions; furthermore, the method forblood glucose monitoring may be referred to the third exemplaryembodiment, so that detailed descriptions thereof are not repeated.

Moreover, in the sixth exemplary embodiment, an end of the joint element124 is connected to a light outlet 601 of the portable mobile device600, and another end of die joint element 124 is used for resting on anouter corner of the eye.

On the other hand, the optical kit 604 may further selectively comprisea lens set 608. When the optical kit 604 has the lens set 608, theoptical kit 604 may be integrated as a camera lens in camera module ofthe portable mobile device 600. In addition, whether or not the opticalkit 604 has the lens set 608, the camera lens in the camera module ofthe portable mobile device 600 camera module may be replaced by theoptical kit 604 in order to perform the blood glucose monitoring. Inanother exemplary embodiment, during the blood glucose monitoring, theoptical kit 604, with the design of the light source, may be externallyattached directly on the camera lens of the camera module of theportable mobile device 600.

In the present exemplary embodiment, the light 110 emitted from thelight source 102 is directed into the eyeball 200 and focused on theeyeball 200 through the first beam splitter 104. The set of photodetectors 606 is, for example, used to measure the light 110 reflectedfrom the eyeball 200 and then passed through or reflected from the firstbeam splitter 104. The light 110 to be measured is first transmitted tothe optical angular measuring device 612 for measuring the opticalangular information, and then transmitted to the energy measuring device614 for measuring the absorption energy information.

According to the above descriptions, the portable mobile device 600 ofthe sixth exemplary embodiment may simultaneously analyze the opticalangular difference and the absorption energy difference between thelight 110 emitted from the light source 102 and the light 110transmitted to the set of photo detectors 606, thus obtaining a glucoseinformation (e.g., glucose value), and since the concentration ofglucose in the eyeball 200 (e.g., aqueous humor within eyeball) has acorresponding relationship with the concentration of blood glucose, ablood glucose information (e.g., blood glucose value) with high accuracyis read through the corresponding relationship. In addition, since theblood glucose monitoring function is integrated to the portable mobiledevice 600, it is convenient in utilization. Moreover, telemedicine caremay be provided by using the program or network of the portable mobiledevice 600 to connect to the cloud.

FIG. 7 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with aseventh exemplary embodiment.

Referring to FIG. 6 and FIG. 7, a difference between a portable mobiledevice 700 of the seventh exemplary embodiment and the portable mobiledevice 600 of the sixth exemplary embodiment is that the portable mobiledevice 700 further comprises the second beam splitter 404 (may bereferred to the third exemplary embodiment), and the set of photodetectors 606 further comprises an optical rotatory distributionmeasuring device 616 and an energy measuring device 618. The opticalrotatory distribution measuring device 616 is, for example, an activeoptical rotatory distribution measuring device or a passive opticalrotatory distribution measuring device. The energy measuring device 618is, for example, a light sensing element, such as a charge coupleddevice, a complementary metal oxide semiconductor sensors or a lightemitting diode. Compositions, coupling relations and functions of theother components of the portable mobile device 700 of the seventhexemplary embodiment are similar to that of the portable mobile device600 of the sixth exemplary embodiment, and the similar components of theportable mobile device 700 of the seventh exemplary embodiment and ofthe portable mobile device 600 of the sixth exemplary embodiment arewith similar compositions; furthermore, the method for blood glucosemonitoring may be referred to the third exemplary embodiment, so thatdetailed descriptions thereof are not repeated.

The second beam splitter 404 is, for example, to transmit the reflectedlight 111 reflected from the eyeball 200 and then transmitted throughthe first beam splitter 104 to the set of photo detectors 606. Thesecond beam splitter 404 is, for example, an optical film, an opticallens, an optical grating, a diffractive optic element, or a combinationof any the above elements.

In the set of photo detectors 606, the optical angular measuring device612 and the energy measuring device 614 are, for example, used formeasuring a ray of light 110 reflected from the eyeball 200 and thenpassed through the first beam splitter 104 reflected from the eyeball200 and then passed through the first beam splitter 104. The light 110 cto be measured is, for example, first transmitted to the optical angularmeasuring device 612 for measuring the optical angular information, andthen transmitted to the energy measuring device 614 for measuring theabsorption energy. The optical angular measuring device 616 and theenergy measuring device 618 are, for example, used for measuring a rayof light 110 d reflected from the eyeball 200, transmitted to the secondbeam splitter 404 through the first beam splitter 104 to the, and thenreflect by the second beam splitter 404. The light 110 d to be measuredis, for example, first transmitted to the optical angular measuringdevice 616 for measuring the optical angular information, and thentransmitted to the energy measuring device 618 for measuring theabsorption energy information.

In the present exemplary embodiment, the energy measuring devices 614,618 are described as two separate components; however, in anotherexemplary embodiment, the energy measuring devices 614, 618 may be aplurality of different sensing regions on the same light sensing elementand may also use the different sensing regions on the light sensingelement to sense the light.

Similarly, the portable mobile device 700 of the seventh exemplaryembodiment may simultaneously analyze the optical rotatory distributiondifference and the absorption energy difference between the light 110emitted from the light source 102 and the reflected light 111 c, 111 dtransmitted to the set of photo detectors 606, thus obtaining theglucose information (e.g., concentration of glucose), and since theconcentration of glucose in the eyeball 200 (e.g., aqueous humor withineyeball) has a corresponding relationship with the concentration ofblood glucose, the blood glucose information (e.g., concentration ofblood glucose) with high accuracy is read through the correspondingrelationship. In addition, since the blood glucose monitoring functionis integrated to the portable mobile device 700, it is convenient inutilization. Moreover, telemedicine care may be provided by using theprogram or network of the portable mobile device 700 to connect to thecloud.

FIG. 8 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with aneighth exemplary embodiment.

Referring to FIG. 7 and FIG. 8, a difference between a portable mobiledevice 800 of the eighth exemplary embodiment and the portable mobiledevice 700 of the seventh exemplary embodiment is that, in the portablemobile device 700, the light 110 may generate two rays of reflectedlight 110 f 111 e, 111 f after passed through the first beam splitter104, thus not having the second beam splitter 404 in the portable mobiledevice700. In addition, the set of photo detectors 606 of the portablemobile device 800 has only the energy measuring device 614 not theenergy measuring device 618. The energy measuring device 614 comprises aplurality of sensing regions 614 a, 614 b, wherein the sensing regions614 a, 614 b may respectively measure the absorption energy informationof the reflected light 111 e, 111 f. Compositions, coupling relationsand functions of the other components of the portable mobile device 800of the eighth exemplary embodiment are similar to that of the portablemobile device 700 of the seventh exemplary embodiment, and the similarcomponents in the eighth exemplary embodiment and in the seventhexemplary embodiment are with similar compositions; furthermore, themethod for blood glucose monitoring may be referred to the seventhexemplary embodiment, so that detailed descriptions thereof are notrepeated.

In the present exemplary embodiment, the same energy measuring device614 is used to measure the reflected light 111 e, 111 f. However, inanother exemplary embodiment, the portable mobile device 800 may alsouse two separate energy measuring devices to measure the reflected light111 e, 111 f.

It is noted that, in the aforementioned exemplary embodiments, thereflected light 111 being divided into two rays of reflected light 111e, 111 f by the first beam splitter 104 is taken as an example for thedescription, but the disclosure is not limited thereto. One of ordinaryskill in the art would be able to know that, according to the aboveexemplary embodiments, when the reflected light 111 is divided into twoor more rays of light by the first beam splitter 104, the number of thesensing regions on the energy measuring device 614 may also be dividedinto two or more, so as to respectively correspond to the light from thefirst beam splitter 104, and thus capable of measuring the absorptionenergy information of the corresponded light, respectively.

Although, in the present embodiment, the two or more rays of the lightreceived by the energy measuring device 614 is generated by the firstbeam splitter 104, but the disclosure is not limited thereto. In anotherexemplary embodiment, the two or more rays of the light received by theenergy measuring device 614 may also be formed by the light source 102;therefore, the light passed through the first beam splitter 104 may bemore than two, and now the number of the sensing regions on the energymeasuring device 614 may also be divided into more than two, so as torespectively correspond to the light from the first beam splitter 104,and thus capable of measuring the absorption energy information of thecorresponded light, respectively.

Similarly, the portable mobile device 800 of the eighth exemplaryembodiment may simultaneously analyze the optical angular difference andthe absorption energy difference between the light 110 emitted from thelight source 102 and the light 110 e, 110 f transmitted to the set ofphoto detectors 606, thus obtaining the glucose information (e.g.,glucose value), and since the concentration of glucose in the eyeball200 (e.g., aqueous humor within eyeball) has a correspondingrelationship with the concentration of blood glucose, the blood glucoseinformation (e.g., blood glucose value) with high accuracy is readthrough the corresponding relationship. In addition, since the bloodglucose monitoring function is integrated to the portable mobile device800, it is convenient in utilization. Moreover, telemedicine care may beprovided by using the program or network of the portable mobile device800 to connect to the cloud for using the real-time blood glucose datato remind or control medication and to directly inform the medical unitto perform first aid in case of emergency situation.

FIG. 9 is a schematic diagram illustrating a portable mobile device witha non-invasive blood glucose monitoring function in accordance with aninth exemplary embodiment.

Referring to FIG. 7 and FIG. 9, a difference between a portable mobiledevice 900 of the ninth exemplary embodiment and the portable mobiledevice 700 of the seventh exemplary embodiment is that the compositionof an optical kit 904 of the ninth exemplary embodiment is differentfrom the composition of the optical kit 604 of the seventh exemplaryembodiment. The optical kit 904 is externally attached and disposed onthe device body 602, and the optical kit 904 other than comprises thefirst beam splitter 104 and the lens set 608, also comprises the lightsource 102 and the second beam splitter 404. In addition, the opticalkit 904 may further selectively comprise the light information analysisunit 116 and the alarm 118. Compositions, coupling relations andfunctions of the other components of the portable mobile device 900 ofthe ninth exemplary embodiment are similar to that of the portablemobile device 700 of the seventh exemplary embodiment, and the similarcomponents in the ninth exemplary embodiment and in the seventhexemplary embodiment are with similar compositions; furthermore, themethod for blood glucose monitoring may be referred to the seventhexemplary embodiment, so that detailed descriptions thereof are notrepeated.

Similarly, the portable mobile device 900 of the ninth exemplaryembodiment may simultaneously analyze the optical angular difference andthe absorption energy difference between the light 110 emitted from thelight source 102 and the light 110 c, 110 d transmitted to the set ofphoto detectors 606, thus obtaining the glucose information (e.g.,glucose value), and since the concentration of glucose in the eyeball200 (e.g., aqueous humor within eyeball) has a correspondingrelationship with the concentration of blood glucose, the blood glucoseinformation (e.g., blood glucose value) with high accuracy is readthrough the corresponding relationship. In addition, since the bloodglucose monitoring function is integrated to the portable mobile device800, it is convenient in utilization. Moreover, telemedicine care may beprovided by using the program or network of the portable mobile device800 to connect to the cloud.

It is noted that the concept of the externally connected optical kit 904of the portable mobile device 900 in the ninth exemplary embodiment mayalso be applied to the sixth to the eighth exemplary embodiment.

FIG. 10 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance witha tenth exemplary embodiment.

Referring to FIG. 6 and FIG. 10, a difference between a portable mobiledevice 1000 of the tenth exemplary embodiment and the portable mobiledevice 600 of the sixth exemplary embodiment is that the composition ofan optical kit 1004 of the tenth exemplary embodiment is different fromthe composition of the optical kit 604 of the sixth exemplaryembodiment. The optical kit 1004 is externally attached and disposed ona lens 1006 of the portable mobile device 1000, and the optical kit 1004comprises the first beam splitter 104, the light source 102 and theoptical rotatory distribution measuring device 612. In addition, theoptical kit 1004 may further selectively comprise the light informationanalysis unit 116 and the alarm 118. One of ordinary skill in the artwould be able to couple the light source 102, the optical rotatorydistribution measuring device 612 and the light information analysisunit 116 with the processing unit 108 using the most suitable method, sothat detailed descriptions are not repeated. Compositions, couplingrelations and functions of the other components of the portable mobiledevice 1000 of the tenth exemplary embodiment are similar to that of theportable mobile device 600 of the sixth exemplary embodiment, and thesimilar components in the tenth exemplary embodiment and in the sixthexemplary embodiment are with similar compositions; furthermore, themethod for blood glucose monitoring may be referred to the sixthexemplary embodiment, so that detailed descriptions thereof are notrepeated.

When measuring the blood glucose, the optical angular measuring device612 and the energy measuring device 614 are, for example, used tomeasure the light 110 reflected from the eyeball 200 and then passedthrough the first beam splitter 104. The light 110 to be measured is,for example, first transmitted to the optical angular measuring device612 for measuring the optical angular information, and then transmittedto the energy measuring device 614, after passed through the lens 1006,for measuring the absorption energy information.

Similarly, the portable mobile device 1000 of the tenth exemplaryembodiment may simultaneously analyze the optical rotatory distributiondifference and the absorption energy difference between the light 110emitted from the light source 102 and the reflected light 111transmitted to the set of photo detectors 606, thus obtaining theglucose information (e.g., concentration of glucose), and since theconcentration of glucose in the eyeball 200 (e.g., aqueous humor withineyeball) has a corresponding relationship with the concentration ofblood glucose, the blood glucose information (e.g., concentration ofblood glucose) with high accuracy is read through the correspondingrelationship. In addition, since the blood glucose monitoring functionis integrated to the portable mobile device 1000, it is convenient inutilization. Moreover, telemedicine care may be provided by using theprogram or network of the portable mobile device 1000 to connect to thecloud.

FIG. 11 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance withan eleventh exemplary embodiment.

Referring to FIG. 10 and FIG. 11, a difference between a portable mobiledevice 1100 of the eleventh exemplary embodiment and the portable mobiledevice 1000 of the tenth exemplary embodiment is that, in the portablemobile device 1100, the light 110 may generate two rays of light 110 g,110 h after passed through the first beam splitter 104. In addition, theset of photo detectors 606 of the portable mobile device 1100 comprisesthe optical angular measuring devices 612, 616 and the energy measuringdevice 614. Wherein, the energy measuring device 614 comprises thesensing regions 614 c, 614 d. The light 110 g, 110 h may measure theoptical angular information through the optical angular measuringdevices 612, 616, respectively, and then measure the absorption energyinformation through the sensing regions 614 c, 614 d of the energymeasuring device 614, respectively. Compositions, coupling relations andfunctions of the other components of the portable mobile device 1100 ofthe eleventh exemplary embodiment are similar to that of the portablemobile device 1000 of the tenth exemplary embodiment, and the similarcomponents in the eleventh exemplary embodiment and in the tenthexemplary embodiment are with similar compositions; furthermore, themethod for blood glucose monitoring may be referred to the tenthexemplary embodiment, so that detailed descriptions thereof are notrepeated.

In the present exemplary embodiment, the portable mobile device 1100 maymeasure the reflected light 111 g, 111 h by the same energy measuringdevice 614. However, in another exemplary embodiment, the portablemobile device 1100 may also use two separate energy measuring devices tomeasure the reflected light 111 g, 111 h.

It is noted that, in the aforementioned exemplary embodiments, thereflected light 111 being divided into two rays of reflected light 111g, 111 h by the first beam splitter 104 is taken as an example for thedescription, but the disclosure is not limited thereto. One of ordinaryskill in the art would be able to know that, according to the aboveexemplary embodiments, when the reflected light 111 can be divided intotwo or more rays of reflected light 111 g, 111 h by the first beamsplitter 104, the number of sensing regions on the energy measuringdevice 614 may also be divided into two or more, so as to respectivelycorrespond to the light from the first beam splitter 104, and thuscapable of respectively measuring the absorption energy information ofthe corresponded light.

Although, in the present exemplary embodiment, the two or more rays ofthe light received by the energy measuring device 614 is generated bythe first beam splitter 104, but the disclosure is not limited thereto.In another exemplary embodiment, the two or more rays of the lightreceived by the energy measuring device 614 may also be formed by thelight source 102; therefore, the light passed through the first beamsplitter 104 may be more than two, and now the number of sensing regionson the energy measuring device 614 may also be divided into more thantwo, so as to respectively correspond to the light from the first beamsplitter 104, and thus capable of respectively measuring the absorptionenergy information of the corresponded light.

Similarly, the portable mobile device 1100 of the eleventh exemplaryembodiment may simultaneously analyze the optical angular difference andthe absorption energy difference between the light 110 emitted from thelight source 102 and the light 110 g, 110 h transmitted to the set ofphoto detectors 606, thus obtaining the glucose information (e.g.,glucose value), and since the concentration of glucose in the eyeball200 (e.g., aqueous humor within eyeball) has a correspondingrelationship with the concentration of blood glucose, the blood glucoseinformation (e.g., blood glucose value) with high accuracy is readthrough the corresponding relationship. In addition, since the bloodglucose monitoring function is integrated to the portable mobile device1100, it is convenient in utilization. Moreover, telemedicine care maybe provided by using the program or network of the portable mobiledevice 1100 to connect to the cloud.

FIG. 12 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance witha twelfth exemplary embodiment.

Referring to FIG. 7 and FIG. 12, a difference between a portable mobiledevice 1200 of the twelfth exemplary embodiment and the portable mobiledevice 700 of the seventh exemplary embodiment is that, in the portablemobile device 1200, the light 110 may generate two rays of light 110 i,110 j after passed through the second beam splitter 404. In addition, aset of photo detectors 1206 of the portable mobile device 1200 comprisesa first photo detector 1208 and a second photo detector 1210, and thephoto detector 1208 and the second photo detector 1210 are located at asame side of the second beam splitter 404. In the present exemplaryembodiment, the first photo detector 1208 and the second photo detector1210 are, for example, located at the side of the second beam splitter404 where the light 110 is reflect from, and are respectively used tomeasure two rays of light 110 i, 110 j generated by reflecting the light110 through the second beam splitter 404. Wherein, one of the firstphoto detector 1208 and the second photo detector 1210 is, for example,the optical angular measuring device for measuring the optical angularinformation, and another of the first photo detector 1208 and the secondphoto detector 1210 is, for example, the measuring device for measuringthe absorption energy information. In other exemplary embodiment, thefirst photo detector 1208 and the second photo detector 1210 may alsocomprise the optical angular measuring device and the energy measuringdevice, respectively. The first photo detector 1208 and the second photodetector 1210 are, for example, coupled to the processing unit 108, butthe discourse is not limited thereto. Compositions, coupling relationsand functions of the other components of the portable mobile device 1200of the twelfth exemplary embodiment are similar to that of the portablemobile device 700 of the seventh exemplary embodiment, and the similarcomponents in the twelfth exemplary embodiment and in the seventhexemplary embodiment are with similar compositions; furthermore, themethod for blood glucose monitoring may be referred to the fourthexemplary embodiment, so that detailed descriptions thereof are notrepeated.

In another example embodiment, the first photo detector 1208 and thesecond photo detector 1210 may also located at the side of the secondbeam splitter 404 where the reflected light 111 passes there through,and are respectively used to measure reflected light 111 a, 111 bgenerated by the reflected light 111 after passed through the secondbeam splitter 404.

Similarly, the portable mobile device 1200 of the twelfth exemplaryembodiment may simultaneously analyze the optical angular difference andthe absorption energy difference between the light 110 emitted from thelight source 102 and the light 110 i, 110 g transmitted to the set ofphoto detectors 1206, thus obtaining the glucose information (e.g.,glucose value), and since the concentration of glucose in the eyeball200 (e.g., aqueous humor within eyeball) has a correspondingrelationship with the concentration of blood glucose, the blood glucoseinformation (e.g., blood glucose value) with high accuracy is readthrough the corresponding relationship. In addition, since the bloodglucose monitoring function is integrated to the portable mobile device1200, it is convenient in utilization. Moreover, telemedicine care maybe provided by using the program or network of the portable mobiledevice 1000 to connect to the cloud for using the real-time bloodglucose data to remind or control medication and to directly inform themedical unit to perform first aid in case of emergency situation.

FIG. 13 is a schematic diagram illustrating a portable mobile devicewith a non-invasive blood glucose monitoring function in accordance witha thirteenth exemplary embodiment.

Referring to FIG. 12 and FIG. 13, a difference between a portable mobiledevice 1300 of the thirteenth exemplary embodiment and the portablemobile device 1200 of the twelfth exemplary embodiment is that thecomposition of an optical kit 1304 of the thirteenth exemplaryembodiment is different from the composition of an optical kit 1204 ofthe twelfth exemplary embodiment. The optical kit 1304 is externallyattached and disposed on the device body 602, and the optical kit 1304other than comprises the first beam splitter 104 and the lens set 608,also comprises the light source 102 and the second beam splitter 404. Inaddition, the optical kit 904 may further selectively comprise the lightinformation analysis unit 116 and the alarm 118. Compositions, couplingrelations and functions of the other components of the portable mobiledevice 1300 of the thirteenth exemplary embodiment are similar to thatof the portable mobile device 1200 of the twelfth exemplary embodiment,and the similar components in the thirteenth exemplary embodiment and inthe twelfth exemplary embodiment are with similar compositions;furthermore, the method for blood glucose monitoring may be referred tothe twelfth exemplary embodiment, so that detailed descriptions thereofare not repeated.

Similarly, the portable mobile device 1300 of the thirteenth exemplaryembodiment may simultaneously analyze the optical angular difference andthe absorption energy difference between the light 110 emitted from thelight source 102 and the light 110 i 110 j transmitted to the set ofphoto detectors 606, thus obtaining the glucose information (e.g.,glucose value), and since the concentration of glucose in the eyeball200 (e.g., aqueous humor within eyeball) has a correspondingrelationship with the concentration of blood glucose, the blood glucoseinformation (e.g., blood glucose value) with high accuracy is readthrough the corresponding relationship. In addition, since the bloodglucose monitoring function is integrated to the portable mobile device1300, it is convenient in utilization. Moreover, telemedicine care maybe provided by using the program or network of the portable mobiledevice 1300 to connect to the cloud.

In addition, although the apparatus for non-invasive glucose monitoringused in the application of portable mobile device described the sixth tothe thirteenth exemplary embodiments are taken as examples for thedescriptions, but the disclosure is not limited thereto. One of ordinaryskill in the art would able to refer to the portable mobile device witha non-invasive blood glucose monitoring function disclosed in the sixthto the thirteenth exemplary embodiment to combine the concept of theportable mobile device with a non-invasive blood glucose monitoringfunction with the various implementations of the first to the fourthexemplary embodiments, so as to produce a diversified portable mobiledevice with a non-invasive blood glucose monitoring function.

Moreover, although the first to the thirteenth exemplary embodiments usethe examples of measuring a single eye for the descriptions, but thedisclosure is not limited thereto. One of ordinary skill in the artwould be able to know the method for applying the contents of thepresent disclosure to both two eyes according the aforementionedexemplary embodiments.

FIG. 14 is a schematic diagram illustrating a method for analyzingbiological molecule in accordance with a fourteenth exemplaryembodiment.

The method for analyzing biological molecule in the present embodiment,for example, performs analyzing through the processing unit of anapparatus for biological molecule monitoring. The biological molecule,such as glucose, cholesterol, uric acid, water, lactic acid, urea,ascorbic acid or a combination thereof is analyzed.

Referring to FIG. 14, step S202 may be performed to obtain the opticalangular difference. A method for obtaining the optical angulardifference comprises the following steps. Firstly, a portion of aplurality of optical angular difference values that exceeded anacceptable variation range measured by the apparatus for biologicalmolecule monitoring is discarded. Then, at least one mathematicalstatistical method is used to calculate the optical angular differencevalues. Wherein, the mathematical statistical method is, for example, aleast square error regression analysis method. The acceptable variationrange is, for example, the range represented by the following listedmathematical formulas.

The acceptable variation range for the optical angular difference=thearithmetic mean of the optical angular difference values×(1±15%).

In addition, step S204 may be performed to obtain the absorption energydifference. A method for obtaining the absorption energy differencecomprises the following steps. Firstly, a portion of a plurality ofabsorption energy difference values that exceeded the acceptablevariation range measured by the apparatus for biological moleculemonitoring is discarded. Then, at least one mathematical statisticalmethod is used to calculate the absorption energy difference values.Wherein, the mathematical statistical method is, for example, a leastsquare error regression analysis method. The acceptable variation rangeis, for example, the range represented by the following listedmathematical formulas.

The acceptable variation range for the absorption energy difference=thearithmetic mean of the absorption energy difference values×(1±15%).

Step S206 is performed to establish at least one first polynomialequation representing the relationship between the biological moleculeand the optical angular difference, and at least one second polynomialequation representing the relationship between the biological moleculeand the absorption energy difference. Wherein, the biological moleculecomprises a target molecule and at least one interference molecule, anda plurality of variables of the first polynomial equation and the secondpolynomial equation respectively comprise the target moleculeconcentration and the interference molecule concentration variables.

The first polynomial equation is, for example, established from aplurality of biological molecule concentration values and a plurality ofcorresponding optical angular difference values stored in a database.The second polynomial equation is, for example, established from aplurality of biological molecule concentration values and a plurality ofcorresponding absorption energy difference values stored in thedatabase. Wherein, a plurality of samples of the biological moleculeconcentration values stored in the database comprises a plurality oflive samples or a plurality of standard samples.

In addition, the steps of establishing the first polynomial equation andthe second polynomial equation further comprise distinguishing between aplurality of optical angular difference ranges and a plurality ofabsorption energy difference ranges, having the first polynomialequation correspondingly used in each of the optical angular differenceranges, and having the second polynomial equation correspondingly usedin each of the absorption energy ranges.

For example, when the target molecule is the glucose and theinterference molecule is the lactic acid, and three optical angulardifference ranges and three absorption energy difference ranges aredistinguished, the selected first polynomial equation and secondpolynomial equation are shown below, but the disclosure is not limitedthereto. The first polynomial equation corresponded to the first opticalangular difference range:θ_((glucose effect+lactic acid effect)) =a ₁ X _(glucose concentration)+b ₁ Y _(lactic acid concentration) +c ₁

The first polynomial equation corresponded to the second optical angulardifference range:θ_((glucose effect+lactic acid effect)) =a ₁ ′X _(glucose concentration)+b ₁ ′Y _(lactic acid concentration) +c ₁′

The first polynomial equation corresponded to the third optical angulardifference range:θ_((glucose effect+lactic acid effect)) =a ₁ ″X _(glucose concentration)+b ₁ ″Y _(lactic acid concentration) +c ₁″

wherein, θ_((glucose effect+lactic acid effect)) is the optical angulardifference, X_(glucose concentration) is the target moleculeconcentration variable, Y_(lactic acid concentration) is theinterference molecule concentration variable, a₁, a₁′, a₁″, b₁, b₁′,b₁″, c₁, c₁′ and c₁″ are the known coefficients.

The second polynomial equation corresponded to the first absorptionenergy difference range:P _((glucose effect+lactic acid effect)) =a ₂ X _(glucose concentration)+b ₂ Y _(lactic acid concentration) +c ₂

The second polynomial equation corresponded to the second absorptionenergy difference range:P _((glucose effect+lactic acid effect)) =a ₂ ′X_(glucose concentration) +b ₂ ′Y _(lactic acid concentration) +c ₂′

The second polynomial equation corresponded to the third absorptionenergy difference range:P _((glucose effect+lactic acid effect)) =a ₂ ″X_(glucose concentration) +b ₂ ″Y _(lactic acid concentration) +c ₂″

wherein, P_((glucose effect+lactic acid effect)) is the absorptionenergy difference, X_(glucose concentration) is the target moleculeconcentration variable, Y_(lactic acid concentration) is theinterference molecule concentration variable, a₂, a₂′, a₂″, b₂, b₂′,b₂″, c₂, c₂′ and c₂″ are the known coefficients.

Step S208 is performed, by which the optical rotatory angular differenceand the absorption energy difference measured by the apparatus forbiological molecule monitoring are substituted into the first polynomialequation and the second polynomial equation to calculate a first targetmolecule concentration of the target molecule which simultaneouslyexists in the target molecule and the interference molecule. A methodfor calculating the first target molecule concentration is, for example,solving the simultaneous equations of the first polynomial equation andthe second polynomial equation. During the process of performing stepS208, the optical angular difference and the absorption energydifference are analyzed by controlling the change factor, in order toobtain the first target molecule concentration. Wherein, the changefactor comprises a light emitting frequency, a light energy intensity, alength of turn-on time of the light, a length of turn-off time of thelight, an opto-element offset, or a combination thereof.

In addition, steps S210, S212, S214, S216, S218, or a combinationthereof may be performed selectively.

In step S210, at least one first graph or at least one third polynomialequation representing the relationship between the biological moleculeand the optical angular difference is established. Wherein, the variableof the third polynomial equation comprises the target moleculeconcentration variable.

The first graph and the third polynomial equation, for example, areestablished from the biological molecule concentration values stored inthe database and the corresponding optical angular difference values.Wherein, the samples of the biological molecule concentration stored inthe database comprise a plurality of live samples or a plurality ofstandard samples.

In addition, the steps of establishing the first graph or the thirdpolynomial equation further comprise distinguishing a plurality ofoptical angular difference ranges, having the first graph, the thirdpolynomial equation, or the combination thereof correspondingly used ineach of the optical angular difference ranges.

For example, when the target molecule is the glucose and three opticalangular difference ranges are distinguished, the selected thirdpolynomial equation is shown below, but the disclosure is not limitedthereto.

The third polynomial equation corresponded to the first optical angulardifference range:θ_((glucose effect)) =a ₃ X _(glucose concentration) +c ₃

The third polynomial equation corresponded to the second optical angulardifference range:θ_((glucose effect)) =a ₃ ′X _(glucose concentration) +c ₃′

The third polynomial equation corresponded to the third optical angulardifference range:θ_((glucose effect)) =a ₃ ″X _(glucose concentration) +c ₃″

wherein, θ_((glucose effect)) is the optical angular difference,X_(glucose concentration) is the target molecule concentration variable,a₃, a₃′, a₃″, c₃, c₃′ and c₃″ are the known coefficients.

In step S212, the optical angular difference measured by the apparatusfor biological molecule monitoring is substituted into the first graph,the third polynomial equation or the combination thereof to calculatethe a second target molecule concentration of the target molecule.During the process of performing step S212, the optical angulardifference is analyzed by controlling the change factor, in order toobtain the second target molecule concentration. Wherein, the changefactor comprises the light emitting frequency, the light energyintensity, the length of turn-on time of the light, the length ofturn-off time of the light, the opto-element offset, or the combinationthereof.

In step S214, at least one second graph or at least one fourthpolynomial equation representing the relationship between the biologicalmolecule and the absorption energy difference is established. Wherein,the variable of the fourth polynomial equation comprises the targetmolecule concentration variable.

The second graph and the fourth polynomial equation, for example, areestablished from the biological molecule concentration values and thecorresponding absorption energy difference values stored in thedatabase. Wherein, the samples of the biological molecule concentrationstored in the database comprise a plurality of live samples or aplurality of standard samples.

In addition, the steps of establishing the second graph or the fourthpolynomial equation further comprise distinguishing a plurality ofabsorption energy difference ranges, having the second graph, the fourthpolynomial equation, or the combination thereof correspondingly used ineach of the absorption energy difference ranges.

For example, when the target molecule is the glucose and threeabsorption energy difference ranges are distinguished, the selectedfourth polynomial equation is shown below, but the disclosure is notlimited thereto.

The fourth polynomial equation corresponded to the first absorptionenergy difference range:P _((glucose effect)) =a ₄ X _(glucose concentration) +c ₄

The fourth polynomial equation corresponded to the second absorptionenergy difference range:P _((glucose effect)) =a ₄ ′X _(glucose concentration) +c ₄′

The fourth polynomial equation corresponded to the third absorptionenergy difference range:P _((glucose effect)) =a ₄ ″X _(glucose concentration) +c ₄″

wherein, P_((glucose effect)) is the absorption energy difference,X_(glucose concentration) is the target molecule concentration variable,a₄, a₄′, a₄″, c₄, c₄′ and c₄″ are the known coefficients.

In step S216, the absorption energy difference measured by the apparatusfor biological molecule monitoring is substituted into the second graph,the fourth polynomial equation or the combination thereof to calculate athird target molecule concentration of the target molecule. During theprocess of performing step S216, the absorption energy difference isanalyzed by controlling the change factor, in order to obtain the thirdtarget molecule concentration. Wherein, the change factor comprises thelight emitting frequency, the light energy intensity, the length ofturn-on time of the light, the length of turn-off time of the light, theopto-element offset, or the combination thereof.

In step S218, the first target molecule concentration, the second targetmolecule concentration, the third target molecule concentration or acombination thereof determines a final target molecule concentration. Inother embodiments, when the step S218 is not performed, the first targetmolecule concentration obtained through the step S208 may be used as thefinal target molecule concentration.

According to the fourteenth embodiment, the analysis method of theabove-mentioned biological molecule may obtain the target moleculeconcentration, which simultaneously exists in the target molecule andthe interference molecule through the optical angular difference and theabsorption energy difference; therefore, a more accurate concentrationof target molecule may be obtained.

In summary, the above embodiments at least include the followingfeatures:

1. The apparatus for non-invasive blood glucose monitoring provided bythe aforementioned exemplary embodiments may be used to measure theglucose information accurately (e.g., glucose value) of the measuringobject, and since the concentration of glucose in the eyeball (e.g.,aqueous humor within the eyeball) has a relationship with theconcentration of blood glucose, the blood glucose information (e.g.,blood glucose value) may be read according to the relationship.

2. The portable mobile device with a non-invasive blood glucosemonitoring function provided by the aforementioned exemplary embodimentsmay be miniaturized in applications, so as to improve utilizationconvenience.

3. Utilization environments of the portable mobile device with anon-invasive blood glucose monitoring function provided by theaforementioned exemplary embodiments have no special restriction, thusmay be used indoors and outdoors.

4. The blood glucose value of the measuring object may be continuouslyobtained in real time according to the method for non-invasive bloodglucose monitoring provided by the aforementioned exemplary embodiment.

The analysis method for the biological molecule provided by theaforementioned exemplary embodiment may obtain the target moleculeconcentration which simultaneously exists in the target molecule and theinterference molecule, through the optical angular difference values andthe absorption energy difference values; therefore, a more accurateconcentration of target molecule may be obtained

It will be apparent to those skilled in the art that variousmodifications and variations can be made to the structure of thedisclosed embodiments without departing from the scope or spirit of thedisclosure. In view of the foregoing, it is intended that the disclosurecover modifications and variations of this disclosure provided they fallwithin the scope of the following claims and their equivalents.

What is claimed is:
 1. An apparatus for non-invasive glucose monitoringby measuring at least two properties of reflected light from inside aneyeball and using the at least two properties together to do the glucosemonitoring, comprising: at least one light source, emitting at least oneray of light; a first beam splitter with focusing function transmittingthe light emitted from the light source into an anterior chamber of aneyeball and focusing the light on the anterior chamber of the eyeball,whereby reflected light, reflected from the anterior chamber of theeyeball is generated; a polarizer; a set of light sensing elements,simultaneously measuring the at least two properties of the reflectedlight from the eyeball transmitted onto the set of light sensingelements, wherein one of the at least two properties measured comprisesan absorption energy information of the reflected light transmitted bythe first beam splitter, and another of the at least two propertiesmeasured comprises an optical angular information of the polarized lighttransmitted through the polarizer; and a processing unit, receiving andprocessing the measured optical angular information and the measuredabsorption energy information simultaneously to calculate an opticalangular difference and an absorption energy difference resulting fromthe originating light emitted from the light source, and the polarizedlight and reflected light transmitted to the set of light sensingelements, and using the calculated optical angular difference and thecalculated absorption energy difference to calculate a biologicalmolecule information of a biological molecule by at least two polynomialequations, wherein the at least two polynomial equations comprises afirst polynomial equation and a second polynomial equation, the firstpolynomial equation represents relationship between the biologicalmolecule information and the optical angular difference, and the secondpolynomial equation represents relationship between the biologicalmolecule information and the absorption energy difference; thebiological molecule at least comprises at least a glucose, and theprocessing unit calculates glucose information using the calculatedbiological molecule information.
 2. The apparatus of claim 1, wherein awavelength of the light source is to be absorbed by glucose molecules.3. The apparatus of claim 1, wherein the light source comprises at leastan infrared light.
 4. The apparatus of claim 1, wherein the light sourcecomprises a light emitting diode or a laser diode.
 5. The apparatusclaim 1, wherein the light comprises a linear polarized light, acircular polarized light, an elliptical polarized light or a partialpolarized light.
 6. The apparatus of claim 1, wherein the light sourcehas a function for controlling an emitting frequency of the light, afunction for controlling an intensity of the light, a function forcontrolling a length of a turn-on time of the light, a function forcontrolling a length of a turn-off time of the light or a combinationthereof.
 7. The apparatus of claim 1, further comprising a lightinformation analysis unit for detecting a light information of the lightfrom the first beam splitter before the light is directed into theeyeball, and then the light information is transmitted to the processingunit, an alarm or a light source control unit to perform feedbackcontrol with an optical characteristic of the light.
 8. The apparatus ofclaim 7, wherein the light information analysis unit comprises at leastone of an optical power meter and an optic sensor, the light informationdetected by the optical power meter is an energy information whereas thelight information detected by the optic sensor is at least one of theenergy information and a position information.
 9. The apparatus of claim1, wherein the first beam splitter comprises an optical film, an opticallens, an optical grating, a diffractive optical element or a combinationof any the above elements.
 10. The apparatus of claim 1, wherein anoptical angular measuring device comprises the polarizer and one of thelight sensing elements to measure the optical angular information of thepolarized light, and an energy measuring device comprises another one ofthe light sensing elements to measure the reflected light reflected fromthe eyeball; the optical angular measuring device and the energymeasuring device receive the reflected light reflected by or passedthrough the first beam splitter.
 11. The apparatus of claim 10, whereinthe optical angular measuring device comprises an active measuringdevice or at least one passive measuring device.
 12. The apparatus ofclaim 11, wherein the active measuring device comprises an analyzer,which measures the optical angular information directly.
 13. Theapparatus of claim 11, wherein the passive measuring device comprisesthe polarizer and measures the optical angular information by measuringan energy of the reflected light passed through the polarizer.
 14. Theapparatus of claim 10, wherein the optical angular measuring device andthe energy measuring device are arranged at a same side of the firstbeam splitter, the reflected light through the first beam splitter isfirst transmitted to the optical angular measuring device and thentransmitted to the energy measuring device.
 15. The apparatus of claim10, wherein each light sensing element comprises a charge-coupleddevice, a complementary metal oxide semiconductor sensor or a photodiode.
 16. The apparatus of claim 14, further comprising a light barrierhaving an opening configured to enable the light to pass through theopening of the light barrier, and then transmit to the light sensingelement.
 17. The apparatus of claim 16, wherein the light barriercomprises a metal photomask or a silica glass photomask.
 18. Theapparatus of claim 1, wherein the biological molecule comprises acholesterol, an uric acid, a water, a lactic acid, an urea, an ascorbicacid or a combination thereof.
 19. The apparatus of claim 1, wherein thebiological molecule comprises an interference molecule.
 20. Theapparatus of claim 19, wherein the processing unit removes interferencecaused by the interference molecule during the process of calculatingthe glucose information through the processing unit.
 21. The apparatusof claim 1, wherein the processing unit comprises an analog digitalcircuit integration module, wherein the analog digital circuitintegration module comprises a microprocessor, an amplifier and ananalog digital converter.
 22. The apparatus of claim 21, wherein theanalog digital circuit integration module further comprises a wirelesstransmission device.
 23. The apparatus of claim 1, wherein theprocessing unit analyses the optical angular information and theabsorption energy information from controlling a light quality, anopto-element offset or a combination thereof to calculate the glucoseinformation, and the spatial variation of the light source comprises alight emitting frequency variation, a light energy intensity variation,a length variation of turn-on time of the light or a length variation ofturn-off time of the light or a combination thereof.
 24. The apparatusof claim 1, further comprising a second beam splitter for transmittingthe reflected light reflected from the eyeball and then passing throughor reflected by the first beam splitter to at least one of the set oflight sensing elements.
 25. The apparatus of claim 24, wherein a firstoptical angular measuring device comprises the polarizer and a first oneof the light sensing elements, a first energy measuring device comprisesa second one of the light sensing elements, a second optical angularmeasuring device comprises another polarizer and a third one of thelight sensing elements, and a second energy measuring device comprises afourth one of the light sensing elements; the reflected light passingthrough the second beam splitter is first transmitted to the firstoptical angular measuring device and then transmitted to the firstenergy measuring device, and the reflected light reflected from thesecond beam splitter is first transmitted to the second optical angularmeasuring device and then transmitted to the second energy measuringdevice.
 26. The apparatus of claim 24, wherein a first optical angularmeasuring device comprises the polarizer and a first one of the lightsensing elements, a first energy measuring device comprises a second oneof the light sensing elements, a second optical angular measuring devicecomprises another polarizer and a third one of the light sensingelements, and a second energy measuring device comprises a fourth one ofthe light sensing elements; the reflected light passing through orreflected from the second beam splitter is divided into two rays oflight, one ray is first transmitted to the first optical angularmeasuring device and then transmitted to the first energy measuringdevice, and the other ray is first transmitted to the second opticalangular measuring device and then transmitted to second energy measuringdevice.
 27. The apparatus of claim 24, wherein the second beam splittercomprises an optical film, an optical lens, an optical grating, adiffractive optic element or a combination of any the above elements.28. The apparatus of claim 1, further comprising an eye-alignmentposition device configured to align a sight-line of an eye with theeye-alignment position device for measuring a position of the eyeball.29. The apparatus of claim 28, wherein the eye-alignment position devicecomprises a light spot, a marker or a relief pattern.
 30. The apparatusof claim 1, further comprising a joint element, which is located at alight outlet of the apparatus for non-invasive glucose monitoring, andis used for resting on an outer corner of an eye.
 31. The apparatus ofclaim 30, further comprising a protective cover, which is disposed on asurface of the joint element that is used for resting on the outercorner of the eye.
 32. The apparatus of claim 31, the protective covercomprises a disposable protective cover.
 33. A portable mobile devicewith a non-invasive blood glucose monitoring function and configured tomeasure at least two properties of reflected light from inside aneyeball and using the at least two properties together to do glucosemonitoring, comprising: a portable device body; at least one lightsource, emitting at least one ray of light; an optical kit, which isdisposed on the device body, comprising a first beam splitter withfocusing function therein, wherein the first beam splitter transmits thelight emitted from the light source into an eyeball and focuses thelight on the eyeball, whereby reflected light, reflected from theeyeball is generated; a polarizer; a set of light sensing elements,simultaneously measuring the at least two properties of the reflectedlight from the eyeball transmitted onto the set of light sensingelements, wherein one of the at least two properties measured comprisesan absorption energy information of the reflected light transmitted bythe first beam splitter, and another of the at least two propertiesmeasured comprises an optical angular information of the polarized lighttransmitted through the polarizer; and a processing unit, which isdisposed in the device body, receiving and processing the measuredoptical angular information and the measured absorption energyinformation simultaneously to calculate an optical angular differenceand an absorption energy difference resulting from the originating lightemitted from the light source, and the polarized light and reflectedlight transmitted to the set of light sensing elements, and using thecalculated optical angular difference and the calculated absorptionenergy difference to calculate a biological molecule information of abiological molecule by at least two polynomial equations, wherein thefirst polynomial equation representing relationship between thebiological molecule information and the optical angular difference, andthe second polynomial equation representing relationship between thebiological molecule information and the absorption energy difference;the biological molecule comprises at least a glucose, and the processingunit calculates glucose information using the calculated biologicalmolecule information, the glucose information has a correspondingrelationship with a blood glucose information, and the blood glucoseinformation is calculated using the corresponding relationship.
 34. Theportable mobile device with a non-invasive blood glucose monitoringfunction according to claim 33, wherein the light source is disposed inthe device body.
 35. The portable mobile device with a non-invasiveblood glucose monitoring function according to claim 33, wherein thelight source is a part of the optical kit.
 36. The portable mobiledevice with a non-invasive blood glucose monitoring function accordingto claim 33, wherein a wavelength of the light source comprises aglucose absorbable wavelength.
 37. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 33,wherein a wavelength of the light source comprises a wavelength of aninfrared light.
 38. The portable mobile device with a non-invasive bloodglucose monitoring function according to claim 33, wherein the lightsource comprises a light emitting diode or a laser diode.
 39. Theportable mobile device with a non-invasive blood glucose monitoringfunction according to claim 33, wherein the light comprises a linearpolarized light, a circular polarized light, an elliptical polarizedlight or a partial polarized light.
 40. The portable mobile device witha non-invasive blood glucose monitoring function according to claim 33,wherein the light source has a function for controlling an emittingfrequency of the light, a function for controlling an intensity of thelight, a function for controlling a length of a turn-on time of thelight, a function for controlling a length of a turn-off time of thelight or a combination thereof.
 41. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 33,further comprising a light information analysis unit for detecting alight information of the light from the first beam splitter before thelight is directed into the eyeball, and then the light information istransmitted to the processing unit, an alarm or a light source controlunit to perform feedback control with an optical characteristic of thelight.
 42. The portable mobile device with a non-invasive blood glucosemonitoring function according to claim 41, wherein the light informationanalysis unit comprises at least one of an optical power meter and anoptic sensor, the light information detected by the optical power meteris an energy information, the light information detected by the opticsensor is at least one of the energy information and a positioninformation.
 43. The portable mobile device with a non-invasive bloodglucose monitoring function according to claim 42, wherein at least oneof the optical power meter and the optic sensor is disposed in thedevice body.
 44. The portable mobile device with a non-invasive bloodglucose monitoring function according to claim 42, wherein at least oneof the optical power meter and the optic sensor is a part of the opticalkit.
 45. The portable mobile device with a non-invasive blood glucosemonitoring function according to claim 33, wherein the first beamsplitter focuses the light on an anterior chamber of the eyeball, andthe reflected light reflected from the eyeball comprises the reflectedlight reflected from an aqueous humor.
 46. The portable mobile devicewith a non-invasive blood glucose monitoring function according to claim33, wherein the first beam splitter comprises an optical film, anoptical lens, an optical grating, a diffractive optical element or acombination of any the above elements.
 47. The portable mobile devicewith a non-invasive blood glucose monitoring function according to claim33, wherein an optical angular measuring device comprises the polarizerand one of the light sensing elements to measure the optical angularinformation of the polarized light, and an energy measuring devicecomprises another one of the light sensing elements to measure thereflected light reflected from the eyeball, the optical angularmeasuring device and the energy measuring device receive the reflectedlight reflected by or passing through the first beam splitter.
 48. Theportable mobile device with a non-invasive blood glucose monitoringfunction according to claim 47, wherein the energy measuring device isdisposed in the device body.
 49. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 47,wherein the optical angular measuring device is disposed in the devicebody.
 50. The portable mobile device with a non-invasive blood glucosemonitoring function according to claim 47, wherein the optical angularmeasuring device is a part of the optical kit.
 51. The portable mobiledevice with a non-invasive blood glucose monitoring function accordingto claim 47, wherein the optical angular measuring device comprises anactive measuring device or at least one passive measuring device. 52.The portable mobile device with a non-invasive blood glucose monitoringfunction according to claim 51, wherein the active measuring devicecomprises an analyzer, which measures the optical angular informationdirectly.
 53. The portable mobile device with a non-invasive bloodglucose monitoring function according to claim 51, wherein the passivemeasuring device comprises the polarizer and measures the opticalangular information by measuring an energy of the reflected lightpassing through the polarizer.
 54. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 47,wherein the optical angular measuring device and the energy measuringdevice are arranged at a same side of the first beam splitter, thereflected light through the first beam splitter is first transmitted tothe optical angular measuring device and then transmitted to the energymeasuring device.
 55. The portable mobile device with a non-invasiveblood glucose monitoring function according to claim 33, wherein eachlight sensing element comprises a charge-coupled device, a complementarymetal oxide semiconductor sensor or a photo diode.
 56. The portablemobile device with a non-invasive blood glucose monitoring functionaccording to claim 54, further comprising a light barrier with anopening configured to enable the light to pass through the opening ofthe light barrier, and then transmit to the light sensing elements. 57.The portable mobile device with a non-invasive blood glucose monitoringfunction according to claim 56, wherein the light barrier comprises ametal photomask or a silica glass photomask.
 58. The portable mobiledevice with a non-invasive blood glucose monitoring function accordingto claim 33, wherein the biological molecule comprises a cholesterol, anuric acid, a water, a lactic acid, an urea, an ascorbic acid or acombination thereof.
 59. The portable mobile device with a non-invasiveblood glucose monitoring function according to claim 33, wherein thebiological molecule comprises an interference molecule.
 60. The portablemobile device with a non-invasive blood glucose monitoring functionaccording to claim 59, wherein the processing unit removes interferencecaused by the interference molecule during the process of calculatingthe glucose information through the processing unit.
 61. The portablemobile device with a non-invasive blood glucose monitoring functionaccording to claim 33, wherein the processing unit comprises an analogdigital circuit integration module, wherein the analog digital circuitintegration module comprises a microprocessor, an amplifier and ananalog digital converter.
 62. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 61,wherein the analog digital circuit integration module further comprisesa wireless transmission device.
 63. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 33,wherein the processing unit analyses the optical angular information andthe absorption energy information from controlling a light quality, anopto-element offset or a combination thereof to calculate the glucoseinformation, and the spatial variation of the light source comprises alight emitting frequency variation, a light energy intensity variation,a length variation of turn-on time of the light or a length variation ofturn-off time of the light or a combination thereof.
 64. The portablemobile device with a non-invasive blood glucose monitoring functionaccording to claim 33, further comprising a second beam splitter fortransmitting the reflected light reflected from the eyeball and thenreflected by or passing through the first beam splitter to the set oflight sensing elements.
 65. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 64,wherein the second beam splitter is disposed in the device body.
 66. Theportable mobile device with a non-invasive blood glucose monitoringfunction according to claim 64, wherein the second beam splitter is apart of the optical kit.
 67. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 64,wherein a first optical angular measuring device comprises the polarizerand a first one of the light sensing elements, a first energy measuringdevice comprises a second one of the light sensing elements, a secondoptical angular measuring device comprises another polarizer and a thirdone of the light sensing elements, and a second energy measuring devicecomprises a fourth one of the light sensing elements, all of which aredisposed in the device body; the first optical angular measuring deviceand the first energy measuring device respectively measure the opticalangular information and the absorption energy information of reflectedlight reflected from the eyeball and then transmitted through the firstbeam splitter, and the second optical angular measuring device and thesecond energy measuring device respectively measure the optical angularinformation and the absorption energy information of reflected lighttransmitted through the second beam splitter.
 68. The portable mobiledevice with a non-invasive blood glucose monitoring function accordingto claim 64, wherein a first optical angular measuring device comprisesthe polarizer and a first one of the light sensing elements, a firstenergy measuring device comprises a second one of the light sensingelements, a second optical angular measuring device comprises anotherpolarizer and a third one of the light sensing elements, and a secondenergy measuring device comprises a fourth one of the light sensingelements, all of which are disposed in the device body; the reflectedlight passing through the second beam splitter is first transmitted tothe first optical angular measuring device and then transmitted to thefirst energy measuring device, and the reflected light reflected fromthe second beam splitter is first transmitted to the second opticalangular measuring device and then transmitted to the second energymeasuring device.
 69. The portable mobile device with a non-invasiveblood glucose monitoring function according to claim 64, wherein a firstoptical angular measuring device comprises the polarizer and a first oneof the light sensing elements, a first energy measuring device comprisesa second one of the light sensing elements, a second optical angularmeasuring device comprises another polarizer and a third one of thelight sensing elements, and a second energy measuring device comprises afourth one of the light sensing elements, all of which are disposed inthe device body; the reflected light passing through or reflected fromthe second beam splitter is divided into two rays of light, one ray isfirst transmitted to the first optical angular measuring device and thentransmitted to the first energy measuring device, and the other ray isfirst transmitted to the second optical angular measuring device andthen transmitted to the second energy measuring device.
 70. The portablemobile device with a non-invasive blood glucose monitoring functionaccording to claim 64, wherein an optical angular measuring devicecomprises the polarizer and one of the light sensing elements, and anenergy measuring device comprises another one of the light sensingelements, which are disposed in the device body; the reflected lightreflected by the second beam splitter is measured by one of the opticalangular measuring device and energy measuring device, and the reflectedlight passing through the second beam splitter is measured by the otherone of the optical angular measuring device and energy measuring device.71. The portable mobile device with a non-invasive blood glucosemonitoring function according to claim 64, wherein the second beamsplitter comprises an optical film, an optical lens, an optical grating,a diffractive optical element or a combination of any the aboveelements.
 72. The portable mobile device with a non-invasive bloodglucose monitoring function according to claim 47, wherein when thefirst beam splitter transmits a plurality of rays of light, a pluralityof optical angular measuring devices and a plurality of sensing regionsof the energy measuring device respectively are used to measure theoptical angular information and the absorption energy information of thecorresponding light.
 73. The portable mobile device with a non-invasiveblood glucose monitoring function according to claim 33, wherein theoptical kit further comprises a lens set.
 74. The portable mobile devicewith a non-invasive blood glucose monitoring function according to claim73, wherein the optical kit is integrated as a camera lens in a cameramodule when the optical kit has the lens set.
 75. The portable mobiledevice with a non-invasive blood glucose monitoring function accordingto claim 33, further comprising an eye-alignment position deviceconfigured to align a sight-line of an eye with the eye-alignmentposition device for measuring a position of the eyeball.
 76. Theportable mobile device with a non-invasive blood glucose monitoringfunction according to claim 75, wherein the eye-alignment positiondevice comprises a light spot, a marker or a relief pattern.
 77. Theportable mobile device with a non-invasive blood glucose monitoringfunction according to claim 33, further comprising a joint element,wherein an end of the joint element is connected to a light outlet ofthe portable mobile device with a non-invasive blood glucose monitoringfunction, and another end of the joint element is used for resting on anouter corner of an eye.
 78. The portable mobile device with anon-invasive blood glucose monitoring function according to claim 77,further comprising a protective cover, which is disposed on a surface ofthe joint element that is used for resting on the outer corner of theeye.
 79. The portable mobile device with a non-invasive blood glucosemonitoring function according to claim 78, wherein the protective covercomprises a disposable protective cover.
 80. An apparatus fornon-invasive measuring glucose information of an eyeball by measuring atleast two optical properties of reflected light from the eyeball andusing the at least two properties together to obtain the glucoseinformation, comprising: at least one light source that emits at leastone ray of light; a first beam splitter having focusing function thattransmits the light from the light source into an anterior chamber ofthe eyeball and focuses the light on the anterior chamber of theeyeball, whereby the reflected light is generated from the anteriorchamber of the eyeball; an optical angular measuring device comprises apolarizer and a light sensing element to measure optical angularinformation of the polarized light through measuring energy of thepolarized light; an energy measuring device comprises a light sensingelement to measure absorption energy information of the reflected light;wherein the optical angular measuring device and the energy measuringdevice are located at two opposite sides of the first beam splitter,with the optical angular measuring device receiving one of the reflectedlight passing through and reflected by the first beam splitter, and theenergy measuring device simultaneously receiving the other one of thereflected light passing through and reflected by the first beamsplitter; and wherein the light sensing elements of the optical angularmeasuring device and the energy measuring device simultaneously measurethe optical angular information and the absorption energy information ofthe reflected light; and a processing unit, which is connected to thelight source and the light sensing elements, receives and processes themeasured optical properties of the reflected light to calculate abiological molecule information of a biological molecule by at least twopolynomial equations, wherein the first polynomial equation representingrelationship between the biological molecule information and the opticalangular difference, and the second polynomial equation representingrelationship between the biological molecule information and theabsorption energy difference; the processing unit determines the glucoseinformation of the eyeball using the calculated biological moleculeinformation; the calculated biological molecule information uses boththe optical angular information of the polarized light and theabsorption energy information of the reflected light.